Surgical instruments and techniques for treating gastro-esophageal reflux disease

ABSTRACT

An apparatus to treat tissue in a selected wall region of an esophagus is provided. In one embodiment the apparatus includes an elongate member having a circumference and is sized to be deployed in an esophagus. The apparatus further includes an energy delivery element sized to apply electrical energy to tissue in the esophagus, and to produce a pattern of treated tissue within a less than 180° circumferential portion of the esophagus. The elongate member further includes an expandable structure to stabilize the energy delivery element in physical and electrical contact with tissue.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation application of Ser. No. 11/469,816,filed Sep. 1, 2006, which is a continuation application of Ser. No.11/365,943, filed Mar. 1, 2006, which is a divisional of co-pending U.S.application Ser. No. 10/780,027, filed Feb. 17, 2004 (now U.S. Pat. No.7,008,419), which is a divisional of co-pending U.S. application Ser.No. 09/222,501, filed Dec. 29, 1998 (now U.S. Pat. No. 6,740,082), whichclaims the benefit of provisional U.S. Application Ser. No. 60/086,068,filed May 20, 1998, and entitled “Surgical Instruments and Techniquesfor Treating Gastro-Esophageal Reflux Disease,” each of which isincorporated herein by reference in its entirety and to whichapplications we claim priority under 35 USC § 120.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specificationare herein incorporated by reference to the same extent as if eachindividual publication or patent application was specifically andindividually indicated to be incorporated by reference.

FIELD OF THE INVENTION

This invention relates to instruments and techniques forthermally-mediated therapies of targeted tissue volumes in a patient'sLES (lower esophageal sphincter) to treat gastro-esophageal refluxdisease (GERD) in a minimally invasive manner. The thermally-mediatedtreatment, in a low temperature range, selectively injures cells andproteins within the (LES) to induce a predictable wound healing responseto populate the targeted tissue with collagen matrices as a means ofaltering the bio-mechanical characteristics of the LES. In a slightlyhigher temperature range, an alternative thermally-mediated treatment isused to shrink native collagen fibers within the LES to “model” thedimensions and laxity of the LES. The novel treatment techniques arepreferably performed with a trans-esophageally introduced bougie-typeinstrument and are adapted to take the place of more invasive surgicalmethods for treating GERD (e.g., Nissen fundoplications) in thetreatment of the less severe GERD cases.

BACKGROUND OF THE INVENTION

Gastro-esophageal reflux disease (GERD) is a digestive disorder causedby dysfunction in a patient's lower esophageal sphincter (LES). Innormal swallowing, the LES progressively opens to allow food to passinto the stomach and thereafter tightens to prevent food and stomachacids from flowing back into the esophagus. Gastro-esophageal refluxoccurs when the stomach's contents flow upwardly into the esophagus.Typically, such acid reflux results from anatomic abnormalities in theLES and surrounding structures, such as overly relaxed muscle tonewithin the LES, a shortened esophageal length within the abdominalcavity, insufficient intra-abdominal pressures, and/or from acontributory factor such as a hiatal hernia.

Prolonged acid reflux can cause serious complications such asesophagitis, erosions, esophageal bleeding or ulcers. In addition,chronic scarring caused by acid reflux can cause narrowing or stricturein the esophagus. Some patients develop Barrett's esophagus which is aform of severe damage to the esophageal lining. It is believed thatBarrett's esophagus is a precursor to esophageal cancer.

As many as 20 million American adults suffer from moderate to severeGERD. For chronic GERD and heartburn, a physician may prescribemedications to reduce acid in the stomach, such as H2-blockers(cimetidine, famotidine, nizatidine and ranitidine). Another form ofdrug therapy utilizes a proton pump inhibitor (PPI) that inhibits anenzyme in the acid-producing cells of stomach from producing acid(omeprezole, lansoprezole). Yet another form of drug therapy includesmotility drugs for quickening the emptying of stomach contents(cisipride, bethanechol and metoclopramide). The above-described drugtherapies will reduce acid reflux thus reducing pain to the patient, buteither have no impact on, or even increase alkaline reflux which cancause severe erosions in the esophagus. Further there exists increasingevidence that lifetime drug therapies can result in atrophic gastritisin certain patients, which is known precursor to Barrett's esophagus.

Since GERD us caused by an anatomic (mechanical) defect, certainsurgeries are well suited to correct the defect by effectivelylengthening the LES and/or increasing intraluminal pressures within theLES to prevent acid reflux. The leading surgical procedure is anendoscopic Nissen fundoplication, in which the surgeon develops a fold(plication) in the fundus of the stomach and then wraps and sutures theplication generally around the LES to increase intra-esophagealpressures therein. An endoscopic Nissen fundoplication is difficult toperform and typically requires the use of several disposable surgicalinstruments that are expensive. An open surgery to accomplish a Nissenfundoplication also is possible but undesirable because it requireslengthy postoperative recuperation and results in a long disfiguringupper abdominal incision.

There is therefore a need for a new therapies for treating GERD thatoffer mechanical or biomechanical solutions to the anatomic defect thatunderlies gastro-esophageal reflux. Preferably, such new approaches toalleviate acid reflux will not rely on lifetime drug therapies which donot correct the anatomic defect causing acid reflux.

OBJECTS AND SUMMARY OF THE INVENTION

The principal objects of this invention are to provide instruments andtechniques for least invasive delivery of thermal energy through atissue surface to a targeted tissue volume to accomplish the controlledremodeling of the treated tissue, and may also be referred to as bulkingtissue. The targeted tissues that can be treated in a “least invasive”manner include, but not limited to, soft tissues in the interior of abody (in particular, collagenous tissues such as fascia, ligamentoustissue), collagen-containing walls of vessels and organs, and anatomicstructures having, supporting or containing an anatomic lumen (e.g.,esophagus, urethra) Such tissues hereafter may be referred to as“targeted” tissue volumes or “target sites”.

More particularly, the invention discloses techniques and instrumentsthat utilize radiofrequency (Rf) energy delivery to selectively injurecells and extracellular compositions (e.g., proteins) in a target siteto induce a biological response to the injury—such biological responseincluding cell reproduction to an extent but more importantly thepopulation of the extracellular space with collagen fibers in a repairmatrix. Thus, the controlled alteration or modeling of the structuraland mechanical characteristics of a targeted tissue site is possible bysynthesis of new collagen fibers (or “bulking effects”) therein. Theabove-described objects of the invention are enhanced by controlledmanipulation of certain biophysical characteristics of the target tissueprior to the delivery of Rf energy to induce the injury healing process.Besides the synthesis of collagen matrices, another object of theinvention is the acute shrinkage of native collagen fibers in thetargeted tissue volume. Such acute collagen shrinkage can causetightening of a targeted tissue volume.

The injury healing process in a human body is complex and involves aninitial inflammatory response which in collagenous tissues is followedby a subsequent response resulting in the population of new (nascent)collagen in the extracellular space. A mild injury may produce only aninflammatory reaction. More extensive tissue trauma invokes what isherein termed the injury healing response. Any injury to tissue, nomatter whether mechanical, chemical or thermal may induce the injuryhealing response and cause the release of intracellular compounds intothe extracellular compartment of the injury site. This disclosurerelates principally to induction of the injury healing process by athermally-mediated therapy. The temperature required to induce theresponse ranges from about 40° C. to 70° C. depending on the targetedtissue and the duration of exposure. Such a temperature herein may bereferred to as Tncs (temperature that causes “new collagen synthesis”).The temperature needed to cause such injury and collagen synthesis islower than the temperature Tsc (temperature for acute “shrinkage ofcollagen”) in another modality of the method of the invention disclosedherein.

In order to selectively injure a target tissue volume to induce thepopulation of the extracellular compartment with a collagen matrix,“control” of the injury to a particular tissue is required. In thisdisclosure, a Rf energy source is provided to selectively induce theinjury healing process. (It should be appreciated that other thermalenergy devices are possible, for example a laser). In utilizing an Rfenergy source, a high frequency alternating current (e.g., from 100,000Hz to 500,000 Hz) is adapted to flow from one or more electrodes intothe target tissue. The alternating current causes ionic agitation andfriction in the targeted tissue as the ions follow the changes indirection of the alternating current. Such ionic agitation or frictionalheating thus does not result from direct tissue contact with a heatedelectrode.

In the delivery of energy to a soft tissue volume, I=E/R where I is theintensity of the current in amperes, E is the energy potential measuredin volts and R is the tissue resistance measured in ohms. In such a softtissue volume, “current density” or level of current intensity is animportant gauge of energy delivery which relates to the impedance of thetissue volume. The temperature level generated in the targeted tissuevolume thus is influenced by several factors, such as (i) Rf currentintensity (ii) Rf current frequency, (iii) tissue impedance levelswithin the targeted tissue volume, (v) heat dissipation from thetargeted tissue volume, (vi) duration of Rf delivery, and (vii) distanceof the targeted tissue volume from the electrodes. A subject of thepresent invention is the delivery of “controlled” thermal energy to atargeted tissue volume with a computer controlled system to vary theduration of current intensity and frequency together, based on sensorfeedback systems.

In the initial cellular phase of injury healing, granulocytes andmacrophages appear and remove dead cells and debris. In the inflammationprocess, the inflammatory exudate contains fibrinogen which togetherwith enzymes released from blood and tissue cells, cause fibrin to beformed and laid down in the area of the tissue injury. The fibrin servesas a hemostatic barrier and thereafter acts as a scaffold for repair ofthe injury site. Fibroblasts migrate and either utilize the fibrin asscaffolding or for contact guidance thus further developing a fiber-likescaffold in the injury area. The fibroblasts not only migrate to theinjury site but also proliferate During this fibroplastic phase ofcellular level repair, a extracellular repair matrix is laid down thatis largely comprised of collagen. Depending on the extent of the injuryto tissue, it is the fibroblasts that synthesize the collagen within theextracellular compartment as a form of connective tissue (hereafternascent collagen), typically commencing about 36 to 72 hours after theinjury.

Thus, in the injury healing response, compound tissues or organs arerepaired by such fibrous connective tissue formation (or matrixformation). Such fibrous connective tissue is the single most prevalenttissue in the body and gives structural rigidity or support to tissuesmasses or layers. The principal components of such connective tissuesare three fiber-like proteins-collagen, reticulin and elastin along witha ground substrate. The bio-mechanical properties of fibrous connectivetissue and the repair matrix are related primarily to the fibrousproteins of collagen and elastin. As much as 25% of total body proteinis native collagen. In repair matrix tissue, it is believed that nascentcollagen is in excess of 50%.

The unique properties of collagen are well known. Collagen is anextracellular protein found in connective tissues throughout the bodyand thus contributes to the strength of the musculo-skeletal system aswell as the structural support of organs. Numerous types of collagenhave been identified that seem to be specific to certain tissues, eachdiffering in the sequencing of amino acids in the collagen molecule.

It has been previously recognized that collagen (or collagen fibers aslater defined herein) will shrink or contract longitudinally whenelevated in temperature to the range of 60° C. to 80° C., hereinreferred to as Tsc. Portions of this disclosure relate to techniques forcontrolled shrinkage of collagen fibers in the soft tissue, and moregenerally to the contraction of a collagen-containing tissue volume,(including both native collagen and nascent collagen) for therapeuticpurposes.

Collagen consists of a continuous helical molecule made up of threepolypeptide coil chains. Each of the three chains is approximate equallength with the molecule being about 1.4 nanometers in diameter and 300nm in length along its longitudinal axis in its helical domain domain(medial portion of the molecule). The spatial arrangement of the threepeptide chains in unique to collagen with each chain existing as aright-handed helical coil. The superstructure of the molecule isrepresented by the three chains being twisted into a left-handedsuperhelix. The helical structure of each collagen molecule is bonded totogether by heat labile intermolecular cross-links (or hydrogencross-links) between the three peptide chains providing the moleculewith unique physical properties, including high tensile strength alongwith moderate elasticity. Additionally, there exist heat stabile orcovalent cross-links between the individual coils. The heat labilecross-links may be broken by mild thermal effects thus causing thehelical structure of the molecule to be destroyed with the peptidechains separating into individual randomly coiled structures. Suchthermal destruction of the cross-links results in the shrinkage of thecollagen molecule along its longitudinal axis to up to one-third of itsoriginal dimension, in the absence of tension.

A plurality of collagen molecules (also called fibrils) aggregatenaturally to form collagen fibers that collectively make up the afibrous matrix. The collagen fibrils polymerize into chains in ahead-to-tail arrangement generally with each adjacent chain overlappinganother by about one-forth the length of the helical domain a quarterstagger fashion to form a collagen fiber. Each collagen fiber reaches anatural maximum diameter, it is believed because the entire fiber istwisted resulting in an increased surface are that succeeding layers offibrils cannot bond with underlying fibril in a quarter-stagger manner.

Thus, the present invention is directed to techniques and instrumentsfor controlled thermal energy delivery to portions of a patient's LES,in alternative therapies, either:

a) to selectively injury cells and proteins in walls of the LES toinduce an injury healing response which populates the extracellularcompartment with a collagen fiber matrix (“nascent collagen”) to bulkand alter the architecture and flexibility characteristics of tissuevolumes within walls of the LES; or

b) to, optionally, shrink either “native” collagen or “nascent” collagenin tissue volumes within the wall of the LES to further alter mechanicalcharacteristics of the LES and increase intra-esophageal pressures.

More in particular, the device of the present invention for “modeling” acollagen matrix in targeted tissue (or “bulking” targeted tissue) inwalls of the patient's LES is fabricated as a flexible bougie thatcarries thermal energy delivery means in its distal working end.Typically an Rf source is connected to at least one electrode carried inthe working end. The working end may carry a single electrode that isoperated in a mono-polar mode or a plurality of electrodes operated ineither a mono-polar or bi-polar manner, with optional multiplexingbetween various paired electrodes. A sensor array of individual sensorsalso is carried in the working end, typically including (i)thermocouples and control circuitry, and/or (ii) impedance-measuringcircuitry coupled to the electrode array.

A computer controller is provided, together with the feedback circuitryfrom the sensor systems, that is capable of full process monitoring andcontrol of: (i) power delivery; (ii) parameters of a selectedtherapeutic cycle, (iii) mono-polar or bi-polar energy delivery, and(iv) multiplexing Rf delivery. The controller also can determine whenthe treatment is completed based on time, temperature, tissue impedanceor any combination thereof.

In a first method of the invention, the device is introduced through thepatient's mouth until the working end and electrode array is positionedwithin the LES. The therapeutic phase commences and is accomplishedunder various monitoring mechanisms, including but not limited to (i)direct visualization, (ii) measurement of tissue impedance of the targettissue masses relative to the device, and (iii) utilization ofultrasound imaging before or during treatment. The physician actuatesthe pre-programmed therapeutic cycle for a period of time necessary toelevate the target tissue mass to Tncs (temperature of new collagensynthesis) which is from 45° C. to 60° C. depending on duration ofenergy delivery.

During the therapeutic cycle, the delivery of thermal energy isconducted under full-process feedback control. The delivery of thermalenergy induces the injury healing response which thereafter populatesthe mass with an extracellular collagen matrix and reduces theflexibility of the LES over the subsequent several days and weeks. Thephysician thereafter may repeat the treatment.

In a second method of the invention, (either the initial or a subsequenttherapeutic cycle) the delivery of Rf energy may be elevated to shrinkcollagen fibers at a range between 60° C. to 80° C. to reach Tsc. Theeffect of such collagen shrinkage is to rigidify or bulk the treatedtissue volumes in the wall of the LES.

Following an initial therapeutic cycle, the treatment can be repeateduntil the desired increase in intra-esophageal pressures is achieved. Itis believed that such periodic treatments (e.g., from 2 to 6 treatmentsover a period of several weeks) may be best suited to treat the LES.

The above-described modalities of (i) induced synthesis of collagen incollagenous tissues, and (ii) shrinkage of collagen in collagenoustissues describe the effects on LES tissue volumes. These methods oftreating the LES are defined herein by a particular temperature rangethat causes the exact cellular/extracellular effects in the targetedtissue volumes, and are intended to be inclusive of other descriptiveterms that may be used to more generally characterize treatments, suchas tightening tissue, bulking tissue, fusing or fusion of collagenoustissues, creating scar tissue, sealing or welding collagen-containingtissue, shrinking tissue and the like. The methods disclosed herein arenot defined to include ablating tissue, which occurs at highertemperature levels.

In general, the present invention advantageously provides least invasivethermally-mediated techniques for increasing intraluminal pressures in apatient's LES to prevent gastro-esophageal reflux.

The present invention provides novel devices and techniques forthermally inducing an injury healing response to altercellular/extracellular architecture in the LES.

The present invention provides techniques for thermal induction ofbulking of tissue volumes around a sphincter in an anatomic lumen.

The present invention advantageously provides an electrode array furdelivering a controlled amount of Rf energy to a specific targetedtissue volume in the LES having a particular shape or pattern.

The present invention provides an electrode array for delivering acontrolled amount of Rf energy to a specific target collagen-containingtissue volume to achieve a controlled contraction of the collagen fiberstherein.

The present invention provides a novel device and technique forcontraction of collagen fibers around the lumen of an anatomic structureto reduce the dimension of the lumen.

The present invention also provides an instrument and method in which abougie-type member has a working channel to accommodate an endoscope, anaccessory instrument or for therapeutic agent delivery or suction.

The present invention advantageously provides a device that isinexpensive and disposable. Additional advantages and features of theinvention appear in the following description in which severalembodiments are set forth.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a Type “A” device and Rf energy sourceof the present invention.

FIG. 2 is transverse sectional view of the device of FIG. 1 taken alongline 2-2 of FIG. 1.

FIG. 3 A is an enlarged perspective view of the working end of thedevice of FIG. 1.

FIG. 3B is transverse sectional view of the working end of FIG. 3 Ataken along line 3B-3B of FIG. 3A.

FIG. 4 is a perspective view of an alternative embodiment of working endsimilar to FIG. 3 A.

FIGS. 5A-5F are views of a portion of the wall of a lower esophagealsphincter (LES) showing various patterns of thermally-mediatedtreatments developed by various electrode arrays.

FIG. 6A is a view of an alternative embodiment of working end similar tothat of FIG. 3A.

FIG. 6B is an alternative embodiment of working end showing a workingchannel.

FIG. 6C is a block diagram of the Rf source of the invention including acomputer controller.

FIGS. 7A-7D are schematic views of a method of thermally-mediatedtreatment of the LES utilizing the device of FIG. 1; FIG. 7A being aview of positioning the working end in the region of the LES; FIG. 7Bbeing a view of expansion of an optional balloon carried at the workingend; FIG. 7C being a view of sectional view of the working end takenalong line 7C-7C of FIG. 7B showing the targeted tissue region; and,FIG. 7D showing the tissue dimensions following a thermally mediatedtherapy.

FIGS. 8A-8B are views of the working end of a Type “B” of device forthermally-mediated therapies of the LES and its means of capturing thewall of the LES for treatment.

FIG. 9 is a view of the working end of an alternative Type “B” devicessimilar to the device FIGS. 8A-8B.

FIG. 10 is a view of a portion of the wall of the LES showing a methodof treatment with a Type “B” device.

FIG. 11A is a view of the working end of another alternative Type “B”with rolling components.

FIG. 11B is a view of a portion of the wall of the LES showing a methodof treatment with the working end of FIG. 11A.

FIG. 12A is a view of the working end of yet another Type “B” device.

FIG. 12B is a view of a portion of the wall of the LES showing a methodof treatment with the working end of FIG. 12A.

FIG. 13 A is a view of a Type “C” device system for thermally-mediatedtreatments of the LES.

FIG. 13B is a view of the working end of a component of the Type “C”system of FIG. 13A.

FIG. 13C is a views of an alternative working end similar to that ofFIG. 13B.

FIG. 14 is a view of the wall of the LES showing a method of treatmentwith the Type “C” system of FIG. 13A.

FIG. 15 is a view of the working end of another Type “C” device

DESCRIPTION OF THE PREFERRED EMBODIMENT OF THE INVENTION 1. Type “A”Device for Thermally-Mediated LES Therapy.

By way of example, FIG. 1 depicts LES treatment device 5 that is to beutilized for a thermally-mediated alteration of thecellular/extracellular architecture of a lower esophageal sphincter(LES) while at the same time sizing or gauging the lumen of theesophagus. More in particular, device 5 comprises elongate extensionmember 10 with proximal end 11 and working end 15 with distalmost tip16. Referring to FIGS. 1 and 2, extension member 10 has a generallycylindrical shape along longitudinal axis 17 with an overall length ofapproximately 60 to 90 centimeters. The cross-sectional dimension ofextension member 10 would typically range in diameters from #40 to #60French for various patients having varied esophageal anatomies (but maybe much smaller as described below for introduction through a workingchannel of a flexible gastroscope).

The extension member 10 preferably is capable of bending in anapproximately 1.0 cm radius (or less) and may comprise a flexibleplastic casing 18 with a high-density liquid, gel or other suitableflexible core 19 inside the casing and the tapered tip. The device maycompare in size and flexibility to a commercially available bougie thatis adapted to push through an esophagus to enlarge the lumen, such as abougie manufactured by Pilling Week, 420 Delaware Drive, FortWashington, Pa.

In this Type “A” variant, an Rf energy source 40 is provided fordelivering thermal energy to portions of the LES. The Rf energy source40 may alternatively be replaced with a microwave source, or anotherknown source of thermal energy such as a laser. It further should beappreciated that other sources of energy such as ultrasound orhigh-energy focused ultrasound (HEFU) that are known in the art may beutilized to cause thermally-mediated treatments of target sites in theLES. The Rf energy source 40 is detachably connected to extension member10 by power cable 42.

Referring to FIG. 3A, the working end 15 carries at least one electrodein an electrode array 44, and preferably carries a plurality of Rfelectrodes 45 a-45 n that are positioned in the surface 46 of workingend 15. FIGS. 1 and 3A show two exemplary electrodes 45 a-45 b arrangedlongitudinally in extension member 10 in a spaced relationship insurface 46. The electrodes 45 a-45 b shown in FIG. 3 may be operated ina mono-polar mode (with groundplate) but preferably are operated in abi-polar mode to provide controlled energy delivery to achieve aparticular temperatures between the adjacent paired electrodes 45 a-45 bin the wall W of the LES proximate to the electrodes. The electrodes areof any suitable biocompatible conductive material which conduct currentto and from tissue around the LES in direct contact with electrodes 45a-45 b.

Expansion means are preferably (but optionally) carried in working end15 for increasing the transverse dimension of the working portion andfor pressing any electrodes 45 a-45 n securely against a wall of thelumen of the LES. Inflatable balloon 50 is capable of collapsed andinflated conditions and is depicted in FIG. 1 (phantom view of inflatedcondition) and FIGS. 3A and 3B in an inflated condition. Balloon 50 isincorporated into the wall of extension member 10 in this embodimentgenerally on the opposite side from electrodes 45 a-45 b. Balloon 50preferably is made of an elastomeric material, for example silicone orlatex and has chamber 52 that is inflatable to a maximum transversedimension of approximately 10 to 30 millimeters at low pressures (e.g.,from 0.5 to 5 psi). A Luer-type fitting 53 is coupled to tube 54 that isprovided in core 19 of extension member and communicates with aninflation source to inflate balloon 50, for example a syringe withsaline solution or air (FIG. 1). It should be appreciated that theexpansion means of the invention is shown as balloon 50 but suchexpansion means also may comprise any type of suitable mechanicalexpansion structure disposed within the core of working end 15 that isadapted to expand the cross-section of the working portion that is knownin the art (e.g., flexible ribs that are actuated with a pull cable).

Visible and/or radiopaque and markings 57 are shown in FIG. 1 and areused to both angularly and axially position the working end 15 of thedevice within the patient's LES. The markings 57 in the proximal portionof extension member 10 are useful to the anesthesiologist or physician'sassistant to gauge the depth of insertion of the device as well as itsrotational angle.

As shown in FIG. 3 A, this particular embodiment of device 5 haselectrodes 45 a-45 b each with an elongate shape with the electrodesbeing longitudinally oriented in relation to axis 17 of extension member10. Preferably, the electrodes 45 a and 45 b have a length ranging fromabout 5.0 mm to 15.0 mm and a width ranging from 0.25 mm to 2.5 mm. Thespacing dimension d between the electrodes may range from about 0.5 mmto 10.0 mm.

Although FIGS. 3A-3B show a variant of device 5 with two electrodes 45 aand 45 b, it should be appreciated that a plurality of greater than twoelectrodes may be carried in particular spaced relationships alongworking end 15, as shown in FIG. 4. In FIG. 4, the alternativeembodiment is shown with six longitudinal electrodes 45 a-45 f. Theembodiment of FIG. 4 thus may be operated in a mono-polar mode or in abi-polar mode with a computer controller 60 (see FIG. 1) operativelyconnected to the Rf source 40 and electrodes and temperature sensors tomultiplex (of vector) the current flow between and among various pairedelectrodes. (It should be appreciated that working end 15 may carry onlya single electrode operated in a mono-polar mode and fall within thescope of the invention).

In the preferred embodiment described above, the elongate configurationof the electrodes and their longitudinal orientation was selectedbecause it is believed that Rf energy delivery to elongate regions ofthe LES will prove optimal to accomplish the objectives of methods ofthe invention. As will be described below, functional portions of thelower esophageal sphincter extend as much as several cm from thegastro-esophageal junction and it is believed that the disclosedthermally-mediated treatments of collagen synthesis should extend over asubstantial axial dimension of the LES. Still, another the objective maybe collagen shrinkage based on anatomic dimensions and motility studiesof a particular patient. Further, the diagnosis may indicate that suchcollagen shrinkage is desired in a localized annular or part annularregion. Thus, other electrode patterns in a “Type A” device are possibleand fall within the scope of the invention to deliver particularpatterns of thermally-mediated treatment to the wall W of the LES. FIG.5A shows a singular annular (circumferential) pattern of treated tissueindicated at T in the wall W of a lower esophageal sphincter to shrinkcollagen and slightly reduce the dimension of the lumen by creating bulkin region T. In FIGS. 5A-5F, treated tissue patterns are shown inportions of wall W (member 10 in phantom view) and it can be understoodthat electrodes may be of particular configuration to deliver suchtreatment locations and patterns. (E.g., a single electrode operated ina mono-polar mode (with groundpad) can develop the targeted treatmentband T of FIG. 5 A, or two parallel electrodes operated in a bi-polarmode may cause the targeted treatment band T of FIG. 5 A by energy flowtherebetween). FIG. 5B shows multiple annular regions or bands oftreated tissue T. FIG. 5C illustrates a multiplicity of treatmentregions T as when the objective is the delivery of Rf energy in adiffuse manner over a substantial portion of wall W. FIG. 5D illustratesa plurality of helical treatment regions T which would result in diffuseeffects if the regions were close together. FIG. 5E illustrates av-shaped or chevron-shaped treatment regions T. FIG. 5F is a moregreatly enlarged view of wall W with treated regions T multipleelectrodes 45 a-45 n in phantom view. FIG. 5F shown various arrows Athat indicate multiplexed vectors of current delivery are possible tocause the thermally-mediated treatments of regions T. Any of theelongate electrodes of FIG. 5A-5E may be configured as multipleintermittently-spaced electrodes and optionally may operate in abi-polar and multiplexed mode with varied possible vectors betweenvarious paired electrodes. Only certain electrodes may delivery current,all for a controlled periods of time. The multiplexer also may cause theRf energy delivery to switch between mono-polar and bi-polar during atreatment.

In the embodiments shown, the electrodes are of any suitable conductivematerial which is adapted to deliver Rf energy to soft tissue in thewalls W of the LES around the esophageal lumen without ablating (andnecrosing) any surface tissue to significant degree. The electrodematerial may include gold, nickel titanium, platinum, stainless steel,aluminum and copper. Each individual electrode of the array is connectedto Rf source 40 and controller 60 by a suitable current-carrying wires61 a-61 n within introducer member 10. The proximal portions of suchcurrent-carrying wires are carried in power cable 42 that connects withRf source 40.

Referring back to FIG. 3 A it can be seen that a sensor array ofindividual sensors 65 a-65 b (an number of sensors are possible) also isprovided in a spaced relationship around working end 15. The sensorarray will typically include thermocouples or thermisters to measuretemperature levels of an electrode or of a portion of the wall W incontact with the sensor. Further, the sensor array includes impedancesensing capabilities (not shown) that measures tissue impedance in aconventional manner between particular electrode elements at thecontroller 60 as described below. Current-carrying wires 66 a-66 b areshown in FIGS. 2-3A are connected to sensors 65 a-65 b. Other wires (notshown) may be provided in the device that could be dedicatedspecifically to measuring tissue impedance. One or more such impedancemonitoring systems may be used to confirm prior to the therapeutic cyclethat a satisfactory coupling of energy will be accomplished. Impedanceis monitored between each electrode and a groundpad when operated in amono-polar mode, or between various electrodes when operated in abi-polar mode.

Another embodiment of a Type “A” device 5 is shown in FIG. 6A wherein anultrasound source 70 may be coupled to one or more ultrasoundtransducers 72 (collectively) in a spaced relationship in working end 15of extension member 10. An output of ultrasound source 70, optionally incombination with Rf source 40, any be adapted to deliver thermal energyto the LES. Each ultrasound transducer 72 may be a piezoelectric crystalmounted on a suitable substrate. A conventional ultrasound lens ofelectrically insulated material is fitted between the exterior ofsurface 18 of working end 15 and the piezoelectric crystal which isconnected by electrical leads in extension member to ultrasound source70. Each ultrasound transducer thus is capable of transmittingultrasound energy into the target tissue of the LES for imaging purposesor high-energy ultrasound (HEFU) to deliver thermal energy.Thermocouples can provide accurate temperature measurements of surfacetemperatures at various points along the esophageal lumen. Such thermalsensors are preferably adjacent to piezoelectric crystals.

FIG. 6B shows another embodiment of device 5 with a working channel 76,with an open proximal end in the proximal end 11 of the device with adistal termination (not shown) at the distal end of the device. Theworking channel 76 may be any suitable dimension, for example from about0.5 mm to 5.0 mm or more, to accommodate a flexible shaft accessoryinstrument (e.g., an endoscope or forceps). Working channel 76 also maybe utilized to deliver therapeutic agents to the patient's stomach or tosuction air or liquid secretions from the stomach.

Referring now to FIG. 6C, a block diagram of the Rf source 40 andcontroller 60 is shown. The controller 60 includes a CPU coupled to theRf source and multiplexer 80 through a bus. Associated with thecontroller system may be a keyboard, disk drive or other non-volatilememory system, along with displays that are known in the art foroperating such a system. The operator interface may include varioustypes of imaging systems for observing the treatment such as thermal orinfrared sensed displays, ultrasonic imaging displays or impedancemonitoring displays. The multiplexer 80 is driven by controller 60(digital computer) which includes appropriate software 82.

In operation, current supplied to individual electrodes 45 a-45 n alongwith voltage may be used to calculate impedance. Thermocouples 65carried in a position proximate to the electrodes together withadditional thermal sensors positioned within the Rf source or generatorare adapted to measure energy delivery (current and voltage) to eachelectrode at the site of targeted tissue during a therapeutic cycle. Theoutput measured by thermal sensors is fed to controller 60 in order tocontrol the delivery of power to each electrode location. The controller60 thus can be programmed to control temperature and Rf power such thata certain particular temperature is never exceeded at a targetedtreatment site. The operator further can set the desired temperaturewhich can be maintained. The controller 60 has a timing feature furtherproviding the operator with the capability of maintaining a particulartemperature at an electrode site for a particular length of time. Apower delivery profile may be incorporated into controller 60 as well asa pre-set for delivering a particular amount of energy. A feedbacksystem or feedback circuitry can be operatively connected to theimpedance measuring system, and/or the temperature sensing system orother indicators and to the controller 60 to modulate energy delivery atRf source 40.

The controller software and circuitry, together with the feedbackcircuitry, thus is capable of full process monitoring and control offollowing process variables: (i) power delivery; (ii) parameters of aselected treatment cycle (time, temperature, ramp-up time etc.), (iii)mono-polar or bi-polar energy, and (iv) multiplexing between variouselectrode combinations. Further, controller 60 can determine when thetreatment is completed based on time, temperature or impedance or anycombination thereof. The above-listed process variables can becontrolled and varied as tissue temperature is measured at multiplesites in contact with the sensor array, as well as by monitoringimpedance to current flow at each electrode which indicates the currentcarrying capability of the tissue during the treatment process.Controller 60 can provide multiplexing along various vectors aspreviously described, can monitor circuit continuity for each electrodeand can determine which electrode is delivering energy.

In FIG. 6C, the amplifier 85 is a conventional analog differentialamplifier for use with thermisters and transducers. The output ofamplifier 85 is sequentially connected by analog multiplexer 80 to theinput of analog digital converter 86. The output of amplifier 85 is aparticular voltage that represents the respective sensed temperatures.The digitized amplifier output voltages are supplied to microprocessor88. Microprocessor 88 thereafter calculates the temperature and/orimpedance of the tissue site in question. Microprocessor 88 sequentiallyreceives and stores digital data representing impedance and temperaturevalues. Each digital value received by microprocessor corresponds to adifferent temperature or impedance at a particular site.

The temperature and impedance values may be displayed on operatorinterface as numerical values. The temperature and impedance values alsoare compared by microprocessor with programmed temperature and impedancelimits. When the measured temperature value or impedance value at aparticular site exceeds a pre-determined limit, a warning or otherindication is given on operator interface and delivery of Rf energy to aparticular electrode site can be decreased or multiplexed to otherelectrodes. A control signal from the microprocessor may reduce thepower level at the generator or power source, or de-energize the powerdelivery to any particular electrode site. Controller 60 receives andstored digital values which represent temperatures and impedance sentfrom the electrode and sensor sites. Calculated skin surfacetemperatures may be forwarded by controller 60 to display and comparedto a predetermined limit to activate a warning indicator on the display.

2. Method of Use of Type “A” Device.

Operation and use of the instrument shown in FIG. 1 (with two electrode45 a-45 b embodiment) in performing the method of the present inventioncan be described briefly as follows (FIGS. 7A-7D). The physician or anassistant introduces working end 15 of device 5 through the patient'smouth into lumen 100 of esophagus 102. Referring to FIG. 7A, thephysician advances extension member 10 distally and rotationally untilworking end 15 and electrodes 45 a and 45 b are in a suitable positionwithin the LES (see FIG. 7A). The physician also may advance and turnthe instrument to a correct angle by reference to markings 57 on theproximal portion of the device (see FIG. 1). In the illustrations, it isassumed that the targeted tissue is in a quadrant at the patient's leftside or at the anterior of the LES (see FIGS. 7A-7B). It is believed thearea of treatment will vary from patient to patient as determined bymotiliry studies and anatomic characteristics, and probably most caseswill involve treatments in several angular positions within the LES.

Referring to FIG. 7B, the diameter of extension member 10 may fitsomewhat loosely or snugly in esophageal lumen 100 depending on thediameter of device selected. As shown in FIG. 7C, the physicianpreferably (but optionally) inflates balloon 50 with an inflationmedium, for example air or saline solution from a syringe (not shown).Balloon 50 is inflated to a sufficient dimension to press the surface ofworking end 15, and more particularly electrodes 45 a and 45 b, intofirm contact with surface 104 of targeted tissue in wall W of the LES.(It should be appreciated that a flexible fiberscope 105 (phantom view)may introduced through a optional working channel 76 to view thegastro-esophageal junction 108 from inside the patient's stomach 110which may be useful in positioning the device (see FIG. 7B)). Thephysician selects the treatment site based on anatomical knowledge ofthe LES and is thus capable of avoiding thermal energy delivery tocertain areas or sides of the LES if so desired.

Now referring to FIG. 7B, the physician commences the therapeutic phaseof Rf delivery under various monitoring mechanisms, including but notlimited to, (i) measurement of tissue impedance of the target tissue todetermine electrical conductivity between the targeted tissue and theelectrode arrangement of device 5, (ii) utilization of ultrasoundimaging before and/or during treatment to establish a baseline andduty-cycle tissue characteristics for comparative measurements; andoptionally (iii) direct visualization via a fiberscope introducedthrough a working channel into the stomach and articulated (FIG. 7B).Alternatively, a small diameter flexible scope could be positionedwithin lumen 100 to view the location of working end 15. (Anothersimilar alternative of delivering the thermally-mediated treatmentdisclosed herein is to have a small diameter extension member 10 (e.g.,2.0 mm, to 6.0 mm) that can be introduced through the working channel ofa flexible scope). All these approaches are similar and can yield thesame results in the targeted tissue.

Still referring still to FIG. 7B, the physician may actuate thecontroller to perform a first modality of treatment described above as acollagen synthesis modality. The controller actuates a preprogrammedtherapeutic cycle for a period of time necessary to elevate the targetedtissue T to a particular time/temperature range based on feedback fromthe sensor system. The cycle can elevate temperatures in the tissue to arange between 40° C. to 70° C. for a period of time ranging from 60seconds to 10 minutes. More preferably, the therapeutic cycle wouldelevate temperatures in wall W of the LES to a range between 45° C. and65° C. for a period of time ranging from 60 seconds to 5 minutes. Stillmore preferably, the therapeutic cycle would include temperatures in arange between 50° C. and 60° C. for a period of time ranging from 60seconds to 3 minutes. At the particular selected parameters, the thermaleffects will selectively injures cells in and below the surface 104 ofwall W at target sites T thus inducing the desired injury healingresponse. The depth of thermal penetration into the target tissue sitesT is determined by the current intensity and duration, and mostimportantly the thermal relaxation time of the tissue, to preferablyeffect selective heating of tissue at a depth of about 0.5 mm to 2.5 mmfrom the surface 104 of the wall W of the lumen 100.

As can be seen in FIG. 7C, electrodes 45 a and 45 b are in directcontact with tissue surface 104 of wall W along the tissue-electrodeinterface. Preferably, the controller 60 will sense temperatures alongthe tissue-electrode interface by means of the sensor array and/orimpedance monitoring system and maintain temperature at the tissuesurface 104 at a level below that which ablate the surface, generally bylowering the current intensity or making the energy deliveryintermittent. The effect of elevating the temperature of the interior ofwall W of the LES without surface ablation can be accomplished becauseof surface cooling caused by conduction of heat into lumen 100 and theheat-absorbing (heat-sink) characteristics of the working end 15 andextension member 10.

During the therapeutic cycle, the delivery of energy is preferablyconducted under full-process feedback control, and in fact the treatmentphase may require little attention by the physician ft should beappreciated that the target tissue can be treated uniformly, or variousdiscrete portions of the target tissue can be treated selectively. (Inembodiments with a greater number of electrodes, different levels ofcurrent can be delivered to different electrode elements, or current canbe multiplexed through various electrodes along different vectors asdescribed previously).

A follow-on portion of the therapeutic cycle may comprise a diagnosticphase to gauge the success of the treatment. With energy deliveryterminated, diagnosis may be accomplished through (i) directvisualization, (ii) ultrasound imaging, (iv) infrared imaging, or (v)temperature measurements.

Following such a therapeutic cycle to cause collagen synthesis orbulking of target tissue portions around the LES, the patient can returnto normal activities with periodic monitoring of the intra-esophagealpressure of the LES as well as muscle response of the LES inconventional motility studies. Thereafter, the same treatment may berepeated until alterations in cellular/extracellular architectureincreases intraluminal pressures within the LES to the desired level. Itis believed that periodic treatments (e.g., 1 week to 2 weeks betweentreatments) is best suited to alter the mechanical characteristics ofthe LES. The thermally-mediated treatment induces a bodily responsewhich includes populating the targeted tissue sites T with nascentcollagen in the extracellular spaces, which after periodic treatmentswill make walls W of the LES to be bulked up or thicker and which willcause a reduced cross-section of lumen 100 within the LES.

If the physician elects to tighten the LES to a greater extent, he mayin an initial treatment or in subsequent treatment, perform a differentmodality of thermally-mediated treatment described above as the collagenshrinkage modality. In this case, the physician elects to deliverelevated levels of Rf energy to contract or shrink collagen fibers tofurther tighten or reduce the flexibility of target tissue T within wallportions of the LES. The delivery of Rf energy will shrink collagenfibers as described above in the LES without significant modification ofadjacent tissue volumes. The temperature gradients described above canbe accomplished to achieve the temperature to contract collagen fibersin the targeted tissue without increasing the temperature of the surface104 so that the surface tissue will not be ablated, blistered ornecrosed. The energy level is monitored and controlled as to eachindividual electrode as detailed above by controller 60. The energydelivery is continuously changed based on sensor inputs which includestemperature data and impedance data from the sensors provided in thedevice.

In the collagen shrinkage modality of treatment, a pre-programmedtherapeutic cycle is selected to achieve shrinkage of native collagen.In this case, the delivery of energy is controlled to elevatetemperatures in target tissue T to a range generally between 60° C. to80° C. Preferably, the therapeutic cycle can be controlled to attaintemperatures in the targeted tissue in a range from 60° C. and 70° C.for a period of time ranging from 60 seconds to 5 minutes. Immediateacute longitudinal shrinkage of collagen fibers and molecules will occurin such a temperature range. Thus, the targeted tissue T shrinkgenerally in the direction of collagen fibers therein and will make thewalls around the lumen of the esophagus somewhat tighter and resistantto radial extension (opening). Looking at the thermally-mediated effectson such collagenous tissue from a different perspective, the collagenfibers and molecules are increased greatly in caliber, as describedabove, thus causing a bulking up of the targeted tissue in the LES (seeFIG. 7D). In other words, the native collagen (and collagen matrices)will bulk up and tighten the targeted tissue sites T as shown in FIG.7D. If the therapy is performed following a prior collagen synthesistreatment at the lower temperature ranges described above, the followcollagen shrinkage therapy can be enhanced since both the nascent andnative collagenous tissue will shrink within the target tissue sites T.Each subsequent treatment not only will populate the tissue sites T withadditional nascent collagen fibers, but also shrinks the nascentcollagen fibers from the prior treatment or treatments.

3. Type “B” Device for Thermally-Mediated LES Therapy.

By way of example, FIGS. 8A-8B and 9 depict an alternative type of LEStreatment device that may be utilized for Rf energy delivery to wallportions W of the LES to alter its cellular/extracellular architecture.More in particular, the system includes an embodiment of elongate deviceor member 205 with a medial extending portion 206 that is substantiallysimilar to the Type “A” device described above, and elements common toboth the Type “A” and Type “B” embodiment will be described with thesame reference numerals. As shown in FIG. 8A-8B, the working end 215 ofthis embodiment carries a tissue-engaging means known in the artcomprising an openable/closeable arm structure for engaging targettissue in the wall of the LES (Cf. the openable/closeable arm structureof related Provisional Application Ser. No. 60/024,974 filed on Aug. 30,1996; and follow-on patent application Ser. No. 09/920,291 filed on Aug.28, 1997, which disclosures are incorporated herein in their entirety bythis reference). FIG. 8A shows a longitudinally-oriented arm structurewith arm elements 216 a and 216 b that are rotatable around pivots 217 aand 217 b and are optionally covered within a thin flexible sheath 218that carries longitudinal electrodes 245 a and 245 b. FIG. 8B shows thatarm elements 216 a and 216 b are articulatable from a proximal handle ofthe device by cables and articulating means known in the art thereby tocapture tissue of wall W therebetween. It should be appreciated that theelectrodes may be carried directly on the arm elements without acovering sheath. The sheath, however, is preferred to make theinstrument perform similar to a bougie for ease of introduction into apatient's esophagus.

Referring to FIG. 9, the elongate device 205 further may include aninflatable collar 220 that can be inflated with any suitable medium, forexample air or saline solution from a syringe (not shown). Collar 220 isshown in phantom view in an inflated condition and is position around adistal portion of the device. Collar 220 is sufficiently large toprevent it from passing through GE-junction as the device is liftedproximally and thus may serve as a means of positioning electrodes 245 aand 245 b and the articulating arm elements in the LES.

In operation, a portion of the wall of the LES is shown in sectionalview in FIG. 10 being captured and engaged by arm elements 216 a and 216b (phantom view) of working end 215. The sectional view depicts thetargeted tissue T as a hatched regions in interiors of the wall W of theLES as when Rf energy is delivered in a bi-polar manner between thepaired electrodes (mono-polar flow also is possible). The treatment maybe in a single location or repeated in a plurality of locations. Inorder for the arm elements and sheath 218 to better engage the well ofthe LES, gripping elements known in the art may be configured in thesheath or arm elements to grip tissue (e.g., penetrating elements;tissue gripping studs, or suction apertures communicating with remotesuction source) and are intended be encompassed by the scope of theinvention.

FIG. 11A illustrates another embodiment of Type “B” device in whichroller elements 250 a and 250 b are carried in arm elements 216 a and216 b to progressively the engage the wall W of the LES and delivery Rfenergy between various paired electrodes 245 a-245 n in the rollerelements 250 a and 250 b. This manner of Rf energy delivery wasdisclosed in Provisional Application Ser. No. 60/024,974 filed on Aug.30, 1996 and follow-on patent application Ser. No. 09/920,291 filed onAug. 28, 1997, and incorporated therein Provisional Application Ser. No.60/022,790 filed on Jul. 30, 1996 titled Less Invasive SurgicalInstruments and Techniques for Treating Sleep Apnea and Snoring; all ofwhich applications are incorporated herein in their entirety by thisreference. (In the earlier disclosures, one of the applications of Rfenergy delivery was to model the flexibility of a patient's soft palateby means of collagen synthesis and/or collagen shrinkage therein). FIG.11B is a sectional view of a small portion of the LES with a wall Wengaged between rollers 250 a and 250 b and targeted tissue T receivingRf energy as described above.

Another variant of Type “B” device is shown in FIG. 12A in whicharticulating arm elements 252 a and 252 b are carried in a manner toengage the wall W of the LES at 90.degree. to the previously describedembodiment. In other words, the articulating elements 252 a and 252 bare adapted to capture a portion of wall W treat tissue in a fold arounda part of a circumference of the LES rather than in a longitudinal folddescribed previously. Such a manner of capturing tissue and deliveringRf energy to the wall W of an organ was disclosed in ProvisionalApplication Ser. No. 60/024,974 filed on Aug. 30, 1996 and follow-onpatent application Ser. No. 09/920,291 filed on Aug. 28, 1997(incorporated herein by reference). FIG. 12B is a view of a smallportion of the LES with a wall W engaged by articulating elements 252 aand 252 b and further indicating targeted tissue T receiving Rf energyin any of the manners described previously.

4. Type “C” System for Thermally-Mediated LES Therapy.

By way of example, FIGS. 13A-13C depict an alternative of LES treatmentsystem that may be utilized for performing the above-described methodsof treating a lower esophageal sphincter, but this time with theassistance of a separate device from the exterior of the LES in anendoscopic procedure. At the same time, an intraluminal device is usedto size or gauge lumen 100 of the esophagus 102. More in particular, thesystem includes intraluminal esophageal device 305 which issubstantially similar to the Type “A” device described above, andhereafter will have similar elements described with the same referencenumerals as used above in the Type “A” device. The intraluminal device305 further includes an inflatable collar 307 that can be inflated withany suitable medium, for example air or saline solution from a syringe(not shown). Collar 307 is shown in phantom view in an inflatedcondition and is position around a distal portion of the device. Collar307 is sufficiently large to prevent it from passing through theGE-junction as the device is lifted proximally as a means of positioningelectrodes 45 a-45 n in the LES.

Intraluminal device 305 cooperates with extraluminal device 310 alsoshown in FIG. 13A-13C. The extraluminal device 310 has elongateintroducer member with proximal end 310 a and is adapted forintroduction in the interior of the body through a cannula (e.g., a 5-20mm trocar sleeve) working end 315 is carried in the distal portion ofintroducer member 310 a and comprises an articulatable of flexiblesection 320 section that has a esophagus-contacting surface portion 322.The esophagus-contacting portion 322 may be substantially planar (seeFIG. 13B) but preferably has an at least partial circumferentialreceiving surface 323 for fitting closely around the esophagus 102 whenintraluminal device 305 is positioned within lumen 100 of the esophagus(see FIG. 13C).

As can be seen in FIG. 13A, the extraluminal device 310 has at least oneand preferable a plurality of electrodes 345 a-345 n within working end315. FIG. 14 shows in a (sectional) perspective view that the electrodes345 a-345 n of extraluminal device 310 are adapted to cooperate withelectrodes 45 a-45 b of intraluminal device 305. In use, the electrodesof the two devices, 305 and 310, preferably are adapted to operate in abi-polar manner with current passing from the extraluminal device to theintraluminal device or vice versa, or in a bi-polar manner betweenpaired electrodes in the extraluminal member with the intraluminalelectrodes not activated but facilitating current flow through wall W(or vice versa). Further, the bi-polar operation of the device may bealong a various multiplexed vectors as described previously. Theextraluminal device may have all the temperature sensing capabilities,impedance monitoring capabilities, and other feedback capabilities ofthe Type “A” device described above.

Alternatively, another embodiment of extraluminal device may be used todeliver a thermally-mediated treatment as described above, but only fromthe exterior of the esophagus to targeted tissue in the LES. In somecases, Rf energy delivery only from the exterior of the LES may bepreferred because it would then be unnecessary to elevate thetemperature of surface 104 or mucous membrane of the esophageal lumen100. As described above, the exterior approach logically would beperformed only when the surgeon needed to endoscopically access thepatient's abdominal cavity for other reasons, e.g., to treat a hiatalhernia that sometimes contributes to GERD. Since several ports arenecessary to endoscopically correct a hiatal hernia, the use of such anextraluminal instrument would make such a procedure no more invasive. Ineither a mono-polar or bi-polar operating mode, the intraluminal devicemay simply be a conventional bougie to “stent” the esophagus whileperforming the thermally-mediated Rf treatment of the LES from itsexterior with device 310. FIG. 14 shows the positioning of the devices305 and 310 in a manner of practicing a method of the invention Theextraluminal device may have an articulatable working end so that theesophagus-contacting portion may be easily oriented to lay against theLES. Such a working end may be hinged or flexible by any suitable means(e.g., a pull wire or reciprocating rod mechanism), with the specificarticulation characteristics partly dependent on the location of theport which is used to introduce the device into the patient's body.

FIG. 15 depicts another embodiment of LES treatment device 335 that maybe utilized for thermally-mediated treatment of the LES from itsexterior in an endoscopic procedure. This embodiment of extraluminaldevice has any suitable closing mechanism for closing the at least twoesophagus-contacting portions 336 a and 336 b around the LES andesophagus. Such an embodiment would allow the delivery of thermal energyat least partly around the circumference of the LES, and even entirelyaround the circumference of the LES if so desired. This embodiment wouldrequire that the distal esophagus and LES be mobilized before utilizingthe device. Again, this device would find use in cases that requirerepair of a hiatal hernia wherein mobilization of the distal esophagusis required. As shown in FIG. 15, the two esophagus-contacting portions336 a and 336 b are actuated by reciprocation of sleeve 340 overcam-type elements 342 a and 342 b.

It should be appreciated that the combination of intraluminal andextraluminal devices are preferably indexable by any suitable means, bywhich is meant that it would be desirable to have electrodes of theintraluminal device and the electrodes of the cooperating extraluminaldevice maintainable in a particular alignment or registration, bothaxially and angularly. A preferable means is to provide a fiber opticlight source in the intraluminal component of the system that willtransilluminate the wall W of the LES, thereby allowing the physician toposition markings (or apertures) on the extraluminal device relative tothe points of transillumination. The two esophagus-contacting portionsof the extraluminal instrument are preferably made of a transparentplastic material.

It should be appreciated that the surface 18 of working end 15 may carrycooling means as known in the art, wherein cooling lumens may circulatea coolant fluid within the extension member to maintain the surface 104of the esophageal lumen 100 at a cooled temperature. Alternatively, theextension member may carry the semiconductor Peltier cooling meansdisclosed in co-pending U.S. patent application Ser. No. 09/110,065filed Jul. 3, 1998 titled Semiconductor Contact Lens Cooling System andTechnique for Light-Mediated Eye Therapies. It should also beappreciated that variations on the thermally-mediated treatmentsdisclosed herein may be accomplished with penetrating needle-typeelectrodes in a working end 15 as known in the art that can be actuatedfrom a handle portion of an elongate member although this is not apreferred approach.

From the foregoing it can be seen that there are provided techniques andinstruments that will selectively accomplish thermally-mediatedtreatments of targeted collagenous tissues in a patient's LES withoutsubstantially necrosing or ablating the surface 104 of the esophageallumen 100. The device can be utilized to selectively injure cells toinduce a biological response to populate target tissue site T with acollagen fiber matrix. The device further can be utilized to contractcollagen-containing tissue volumes to reduce the diameter of the lumenof LES. It can be readily understood that such techniques of tissuemodeling may be applied to other lumens of other anatomic structures inthe body. For example, a treatment for urinary incontinence can beeffected to shrink tissue, tighten tissue or rigidify tissue with acollagen matrix around the urethra with a trans-urethral Rf instrument.Similarly, tissues around a patient's soft palates can be treated.Specific features of the invention are shown in some figures and not inothers, and this is for convenience only and any feature may be combinedwith another in accordance with the invention. While the principles ofthe invention have been made clear in the exemplary Type “A” throughType “C” versions, it will be obvious to those skilled in the art thatmodifications of the structure, arrangement, proportions, elements, andmaterials may be utilized in the practice of the invention, andotherwise, which are particularly adapted to specific environments andoperative requirements without departing from the principles of theinvention. The appended claims are intended to cover and embrace any andall such modifications, with the limits only of the true purview, spiritand scope of the invention.

1. An apparatus to treat tissue at a targeted site in an esophaguscomprising: an extension member sized with a central axis for deploymentin an esophagus; an expansion structure on the extension member, and aradio frequency energy delivery element on the extension memberpositioned at a radial position closer to the central axis of theextension member than the expandable structure.